Microstructured implant surfaces

ABSTRACT

An implantable device for treating disc degenerative disease and arthritis of the spine. The implant is sized for placement into an intravertebral disc space. The implant has a body with a predetermined, defined, repeating, three-dimensional pattern at least partially on at least one of its surfaces. The pattern is adapted to create a surface area of bone-contacting features that enhance in-growth and biological attachment to a biocompatible material. Also disclosed are process steps for making the implant.

RELATED APPLICATION

This application is a continuation U.S. patent application Ser. No.13/286,813 filed on Nov. 1, 2011, the contents of which are incorporatedin this application by reference in their entirety and for all purposes.

TECHNICAL FIELD

The present invention relates to microstructured medical implantsurfaces, and to processes for producing such surfaces. This inventionalso relates generally to the treatment of disc degenerative disease orarthritis of the spine and to spinal implants having microstructuredsurfaces used to treat such conditions.

BACKGROUND OF THE INVENTION

In the simplest terms, the spine is a column made of vertebrae anddiscs. The vertebrae provide the support and structure of the spinewhile the spinal discs, located between the vertebrae, act as cushionsor “shock absorbers.” These discs also contribute to the flexibility andmotion of the spinal column. FIG. 1A (described in greater detail below)shows a perspective view of a healthy vertebral column including a discseparating vertebrae.

Over time, the discs may become diseased or infected, developdeformities such as tears or cracks, or simply lose structuralintegrity, for example discs may bulge or flatten. These impaired discscan affect the anatomical functions of the vertebrae, due to theresultant lack of proper biomechanical support, and are often associatedwith chronic back pain. FIG. 1B (also described in greater detail below)shows a perspective view of a vertebral column including a damaged discand vertebrae.

Disc degeneration may occur as part of the normal aging process or as aresult of traumatic injury to the soft and flexible disc positionedbetween the vertebrae. The resulting structural collapse under load maycause, among other things, significant pain and loss of motion. Due tothese conditions, other health issues may result.

Where the goal of the treatment of such health issues is to rigidly fixindividual spinal vertebra after the surgical removal of damaged ordiseased disc tissues, the engagement and subsequent integration ofimplant surfaces in contact with the vertebral bone is required. Rigidfixation helps to enhance immediate recovery from surgery and helps bothin the early stages of healing and over the longer term. Loads throughdaily activities over the longer term are shared between the implanteddevice, or implant, and the resulting osseous (i.e., comprised of,containing, or resembling bone) growth in and around the device.

Some implants are treated using various methods, including coatings,etching processes utilizing chemicals, and acids resulting in roughenedor prepared surfaces that enhance bone in-growth. See, for example, U.S.Pat. No. 5,876,453, No. 5,258,098, U.S. Pat. No. 6,923,810 to Michelsonand U.S. Pat. No. 7,311,734 to Van Hoeck et al., each of which isincorporated by reference herein. The patterns generated in theseprocesses are often intentionally random and irregular. Many acid-etchedsurfaces on implant devices, for example, are random and irregular dueto the application of masking materials in an intentionally randommanner. These surfaces are not optimum because they are inconsistentbetween devices and are difficult to manufacture with precision andrepeatability. Patterned surfaces also typically may have only one depthfrom the original surface and as a result the depth can have too deep afeature that in effect raises stresses between the bone and implants. Byusing multiple cuts of a predetermined depth and overlapping at adesigned interval the overall effect of improved stability is balancedagainst over stressing the osseos interface.

Because bone tissues are organic and irregular in their growth patterns,the tissues will adhere in an irregular manner regardless of the surfacepattern or orientation. This adherence is often sufficient for theinitial stabilization, but not necessarily the most efficient way toprevent movement in the critical early healing phases afterimplantation. Long-term bone in-growth does not necessarily benefit fromthe irregular patterns, but is not necessarily hindered by it either.

The stimulation of bone growth through specific patterns includetextures and roughness in the macro, micron/submicron and nano sizedrange also has benefit when coupled to this regular repeating surfacearchitecture. While osseous tissues do not form in regular 3 dimensionalstructures it does follow a well-established pattern for growth whichour device stimulates through the multiple surface preparation steps.The combination of stress induced remodeling of a stimulated bone cellin apposition to this prepared surface results in the overall deviceenhancing and accelerating the fusion of the device and bone structures.See image of bone structure and the Haversian Canals that typical formin the biologic structure noting the regular patterns at the cellularlevel e.g., Paul R. Odgren et al.; “Bone Structure” Encyclopedia ofEndocrine Disease, Vol. 1, pp. 392-400 (2004) which is incorporated byreference herein.

Optimizing the pattern of the surface, but intentionally removingmaterials in patterns and through defined depths of features (e.g.,teeth, grooves, sharp edges, ridges, anchoring fins (barbs) and shapes(e.g. U.S. Pat. No. 5,207,709, Picha also incorporated by referencedherein), may improve the biological growth of the tissues. Often thisresult is achieved with very large surface features machined or moldedinto implant devices. Larger features have an unintentional anddifficult-to-measure side effect of localizing forces and can, overtime, result in changing osseous integration. Therefore, the devicebecomes less stable or, through stress, induces necrosis remodeling.This is a commonly observed result in orthodontic treatment whereloading is focused to move teeth in a patient's mouth to repositiondentition in a more effective location for mastication and esthetics.Although it is understood that loading can move and reshape bones, eachpatient and even each area of the skeletal structure is variable andtherefore ideal large features often do not work in all applications andall patients. Other factors such as overall health, subsequent healthconditions, degenerative conditions, and traumatic events add to thisdynamic environment.

Other problems confront surgeons. For example, some surfaces are randomand not well suited to the location of implantation, direction ofloading, and forces acting on the implants due to daily activities. Theresults may include poor support of the spinal column or traumaticsurgeries. These, in turn, may result in complications and increasepatient traumatic suffering. Orientation of the surface patterns inparallel to the original surfaces is also enhanced by the depth ofsurface cuts and planes that can be designed to function moreeffectively in resisting directional loading and to be an advantage of adesigned surface having three components, namely the width, length andalso depth of the designed patterns.

To overcome the shortcomings of conventional spinal implants, a newspinal implant having an improved surface treatment is provided. Anobject of the present invention is to provide an implant surface havinga pattern that is substantially uniform over the area of the implantthat is intended to bond to the bone in which the implant is placed. Arelated object is to provide an improved surgically implantable devicehaving on its surface a substantially uniform and bioactivemicromorphology. It is another object of the invention to provide aprocess or processes for manufacturing such improved implant devices. Amore specific object is to provide an improved process that yields asubstantially uniform surface topography designed intentionally toenhance healing and long term function of surgically implantabledevices.

It is to be understood that the present invention while directedprimarily to spinal implants is not limited thereto. The advantageousimplant surface created in practice of this invention obtains asurprising and unexpected osteointegration in the context of spinalrepair that can be applicable in other situations. It is believed thatthe present invention can be applied in many medical circumstances wherebone in-growth to the surface of a prosthetic device is important to thesuccess of the cosmetic or therapeutic procedure. For example, lowerbody bone repair, e.g., foot/ankle, and dental prosthetic proceduresutilizing prosthetic devices where bone in-growth is required are likelyto have their success significantly improved by the use of deviceshaving surfaces produced according to this invention.

SUMMARY OF THE INVENTION

The present invention provides an implantable device comprising a body,the body having a surface and a plurality of connections sized, in oneembodiment, for placement into an intravertebral disc space. The surfacehas a defined, repeating, three-dimensional pattern that provides asurface area of bone-contacting features that allow for and encouragein-growth of bone and proteinaceous materials and biological attachmentto a biocompatible material i.e., integration. The three dimensionalsurface morphology incorporates overlapping patterns of features in twodimensions as well as different and independent thereof dimensionaldepths for each of the features.

Another aspect of the invention is a method of making an implant device,the implant device comprising an implant body, the body defining aworking surface, the surface having a first defined pattern on thesurface; adding a second defined pattern on the surface, the seconddefined pattern overlapping the first defined pattern; and including atleast one other defined pattern on the surface that overlaps with thefirst and second defined patterns.

It is to be understood that both the foregoing general description andthe following detailed description are exemplary, but are notrestrictive, of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention is best understood from the following detailed descriptionwhen read in connection with the accompanying drawings and the attachedclaims. It is emphasized that, according to common practice, the variousfeatures of the drawings are not to scale. On the contrary, thedimensions of the various features are arbitrarily expanded or reducedfor clarity. Included in the drawings are the following figures:

FIG. 1A shows a perspective view of a healthy vertebral column includinga disc separating vertebrae;

FIG. 1B shows a perspective view of a vertebral column including adamaged disc and vertebrae;

FIG. 2 shows a perspective view of a prior art spinal implant;

FIG. 3A shows a perspective view of the spinal implant of the presentinvention;

FIG. 3B shows a partial perspective view highlighting a portion of theimplant illustrated in FIG. 3A;

FIG. 4A shows a partial top view of a surface of the implant of thepresent invention following a first exemplary processing step;

FIG. 4B shows a partial top view of the surface of the implant of thepresent invention shown in FIG. 4A, following a second exemplaryprocessing step;

FIG. 4C shows a partial top view of the surface of the implant of thepresent invention shown in FIG. 4B, following a third exemplaryprocessing step; and

FIG. 4D shows a top view of the completed surface of the implant of thepresent invention following the processing steps shown in FIGS. 4A, 4B,and 4C.

FIGS. 5A, 5B, and 5C show confocal laser microscopy images andaverage-roughness (S_(a)) values of PEEK (A), sTiAIV (B), and rTiAIV (C)surfaces of 644×644 μm² field.

FIGS. 6A, 6B, 6C, 6D, 6E, and 6F show SEM images of PEEK (A, B), sTiAIV(C, D), and rTiAIV (E, F) surfaces at low and high magnifications.

FIG. 7A Shows the three features; Macro, Micron/Submicron and Nano size.

FIG. 7B Shows the size range and roughness of the Macro feature.

FIG. 7C Shows the size range and roughness of the Micron/Submicronfeatures.

FIG. 7D Shows the size range and roughness of the Nano feature.

FIGS. 7A-7D show relative size limitations and surface roughnessfeatures of this invention.

FIG. 8 shows an exemplary dimple pattern surface of this invention inmacroscopic and microscopic detail. The patterns of dimples 1, 2, 3 areoverlapping, but they are sized and aligned so as not to either removethe previous dimple. In FIG. 8 the depth is greatest for 1 and ascendstill step 3 with the sizes of the cuts increasing from 1 to 3.

FIG. 9 is a schematic representation of human osteoblast-like MG63 cellcultures in accordance with an embodiment of the present invention.

FIGS. 10A, 10B, 10C, and 10D are tables showing values obtained fromhuman MG63 osteoblast-like cells harvested 24 hours after confluence onTCPS.

FIGS. 11A, 11B, 11C, and 11D are tables showing values obtained fromhuman MG63 osteoblast-like cells harvested 24 hours after confluence onTCPS.

FIGS. 12A, 12B, 12C, 12D, 12E, 12F, 12G, and 12H are tables showingresults from human MG63 osteoblast-like cells harvested 12 hours afterconfluence on TCPS.

DETAILED DESCRIPTION OF THE INVENTION

Referring now to the drawings, in which like reference numbers refer tolike elements throughout the various figures that comprise the drawings,FIG. 1A shows a spinal column 100 including an upper vertebra 102 and alower vertebra 103 separated by a healthy, flexible disc 104 a. FIG. 1Bshows the spinal column 100 with the upper vertebra 102 and the lowervertebra 103 separated by a damaged or collapsed disc 104 b. The damageddisc 104 b typically requires surgical intervention to attain fusion andstabilization for complete healing and the relief of pain. A deviceaccording to this invention, e.g., a spinal implant, is used to replacethe damaged disc 104 b and provides strong initial stability, rapidhealing, and bone repair.

As illustrated in FIG. 2, certain embodiments of the present inventioninclude an interbody spinal implant 1 that serves as a spacer betweenadjacent vertebrae. The implant 1 may be comprised of titanium, atitanium alloy, organic polymers such as polyaryletheretherketone(“PEEK”) materials, ceramics, and other suitable materials known topeople of skill in the art. The implant 1 comprises an implant body 5with a top surface 10, a bottom surface 20, opposing lateral sides 30,and opposing anterior 40 and posterior 50 portions. The implant 1 has asharp edge 8 where the anterior portion 40 meets the top surface 10 andwhere the anterior portion 40 meets the bottom surface 20. A deliverydevice (not shown) can engage opening 90 in the anterior portion 40 ofthe implant 1, allowing the user to manipulate the implant 1 duringplacement between vertebrae.

The implant 1 is substantially hollow and has a generally oval-shapedtransverse cross-sectional area with smooth and/or rounded lateral sidesand rounded posterior-lateral corners. The implant 1 includes at leastone aperture 60 that extends the entire height of the implant body. Theimplant 1 may further include at least one aperture 70 that extends theentire transverse length of the implant body. These transverse apertures70 may provide improved visibility of the implant 1 during surgicalprocedures to ensure proper implant seating and placement, and may alsoimprove post-operative assessment of implant fusion. Still further, thesubstantially hollow area may be filled with cancellous autograft bone,allograft bone, demineralized bone matrix (DBM), porous synthetic bonegraft substitute, bone morphogenic protein (BMP), or combinationsthereof, to facilitate the formation of a solid fusion column within thepatient's spine.

As illustrated in FIGS. 3A and 3B, the implant 1 further includes adesigned surface topography 80. The designed surface topography 80 isprovided on at least a portion of the top surface 10, the bottom surface20, or both the top and bottom surfaces 10, 20 of the implant 1 forgripping adjacent bone and inhibiting migration of the implant.Preferably, each surface 10 and 20 has a designed surface topography 80that promotes anchoring and healing of spinal tissues.

It is generally believed that the three-dimensional surface of theimplant 1 determines its ultimate ability to integrate into thesurrounding living bone. Without being limited by theory, it ishypothesized that the cumulative effects of at least implantcomposition, implant surface energy, and implant surface topography playa major role in the biological response to, and osteointegration of, theimplant 1.

The addition of macro, micron/submicron and nano sized features in theranges as stated in the table below stimulate the growth of the bonecellular structures by working in concert with well understood bonemodeling and structures. The overall 3 dimensional shape of bone is notof a repeating structure but at a cellular level as in the HaversianCanal the structure is repeating and regular. By stimulating thebiological behavior of the bone cells the resulting stimulation works inconcert with the other structural features of the invention and balancesthe performance of the implant as a fusion device with sufficientresistance to expulsion and mobility to succeed in the initialstabilization of the device and the long term incorporation of rigidfusion of the vertebrae.

Surface Feature Size and Roughness Macro Size Roughness Micron/SubmicronRoughness Nano Size Roughness (Rz) (Ra) Size (Rz) (Ra) (Rz) (Ra) 50μm-200 μm 10 μm-30 μm 500 μm-20 μm 5 μm-10 μm 200 nm-500 nm .5 μm-5 μm

These features in the ranges of peak size or crest to crest of theindentation (Rz) and with an average surface roughness (Ra) are appliedon top of the three machined or etched expulsion features and cover theentirety of the implant and are also on the surfaces of the implant inareas where there is not an anti-expulsion surface pattern. The nanosized features unlike many other published structures are indented intothe surface or subtracted from the base material through post processingetching and blasting methods and therefore have an inherent structuralrigidity that is not found in protruding tube features in the nano sizerange.

“Osteointegration” as that term is used here is intended to mean theformation of a direct structural and functional interface between anartificial implant, and living boned. In a narrower sense,osteointegration occurs without the presence of soft tissue between boneand implant.

Thus, implant fixation may be, at least in part, dependent on theattachment and proliferation of osteoblasts, and like functioning, cellsupon the implant surface. Still further, it appears that these cellsattach more readily to relatively rough surfaces rather than smoothsurfaces. In this manner, a surface may be bioactive due to its abilityto facilitate cellular attachment and osteointegration. Without beinglimited by theory, it is believed that the designed surface topographyand predefined depths of these features 80 may better promote theosteointegration of the implant 1. The designed surface topography 80may also better grip the vertebral endplate surface(s) and inhibitimplant migration upon placement and seating. This is accomplishedthrough the designed patterns of the features including the depths ofthe overlapping patterns.

Thus, the present invention provides the implant 1 having an implantbody 5 that defines a designed surface topography 80 that is both threedimensional and intentionally patterned. The designed surface topography80 is produced in multiple steps using tooling of a specified shape andsize. The designed surface topography 80 is adapted to create a largesurface area of bone-contacting features that allow for in-growth andbiological attachment to a biocompatible material.

The designed surface topography 80 of an implant 1 of this invention hasspecific patterns. By overlapping these patterns, the designed surfacetopography 80 may be used as an integration surface with features of adesirable size for bone growth (specifically implant in-growth) andattachment and to aid in resisting forces that act on the implant 1,thereby improving stability and overall success of the procedure. Thedesigned surface topography 80 with a defined pattern of the implant 1facilitates the installation of the implant 1 and enhances the initial,intermediate, and long-term stability of the implant 1.

The designed surface topography 80 is created using predictable andrepeatable process steps, such as mechanical or chemical machining,photo etching or adaptations of laser or plasma welding technologies.These steps allow for variations of the surface patterns on individualimplant working surface so that areas that may benefit from more or lessaggressive features may be formed. The three dimensional patterns canalso be varied is ways that can be used to fine tune various areas ofthe implant bodies initial fixation due to contact with the vertebralbody and it's relative construction. More specifically, the use ofmicroscopic mechanical or chemical machining, photo etching oradaptations of laser or plasma welding technologies generating repeatingpatterns in multiple overlapping steps onto a surface that is refinedwith e.g., a post machining and abrasive media blasting step, or acidetching, results in a macro and micro designed surface topography 80that effectively integrates with bone. In addition, the designed surfacetopography 80 may be oriented to resist biological loading better thanrandomly generated surfaces.

By analogy, treads on automobile tires are designed with specificfunctions in mind: grip in the forward direction, for example, andstability in the lateral direction. Similarly, the designed selected,planned or strategically chosen surface topography 80 of the presentinvention can be predetermined with specific functions in mind. (By“predetermined” is meant determined beforehand, so that thepredetermined pattern is determined, i.e., chosen, selected or at leastknown or in mind, before processing begins and in view of thepost-implant medical environment). The designed surface topography 80 onthe top surface 10 in the anterior portion 40 may have larger andsharper features to resist expulsion of the implant 1 from between thevertebrae, for example, while the designed surface topography 80 on thetop surface 10 in the posterior portion 50 may have smaller and lesssharp features to facilitate placement of the implant 1. Thisflexibility gives the designer options to achieve desired performancecharacteristics and the designer can both optimize and enhance theperformance of the implant 1 having the designed surface topography 80.Preferably, the implant 1 does not have any unintentional sharp edges orprotrusions (excepting sharp edges 8 which are intentionally provided topermit implant 1 to resist expulsion from between adjacent vertebra).These sharp edges or protrusions sometimes result in focal points forloading and the resulting loss of osseous tissues through stress-inducedbone loss. This is also considered in concert with the structuralproperties of the vertebral body, which is commonly stiffer on the outeredges and has greater mobility towards their center surfaces. Theimplant surface that has synthetic and or biologically derived materialsapplied to it allows for “seeding” in specific locations of thesematerials acting in concert with the microscopic surface enhancementsgenerated in the production process. With or without the addition ofgrowth-enhancing materials and surface geometry, the designed surfacetopography 80 has features in a defined size range that are beneficialto the biological growth and remodeling of bone tissues subjected toloading in several directions.

The designed surface topography 80 of the implant 1 is the connectionpoint for the load-bearing or working surface of the implant 1 and thelive osseous tissue of the vertebrae. The designed surface topography 80allows for initial stabilization and long-term bone in-growth andfusion. Larger surface areas and a smooth and contoured surface providemore assured and effective initial, intermediate, and long-term outcomesand overall benefit to a patient.

Using micro surfaces created through subtractive chemical or mechanicalprocesses is an achievable and commercially viable way to increase thesurface area for dissipating variable loads and compensating forvariable bone conditions. Smaller features that allow for dissipatedforces but having a regulated, designed pattern are beneficial intreating the largest possible number of patients having the largestnumber of variables.

Through careful design of readily available micro machine tools, photoetching, and other processes of microscopic machining and advancedmanufacturing equipment and adaptation of these processes usingrepeating and multiple overlapping patterns of varying depths, surfacesthat have the same roughened contours as chemically etched surfaces maybe achieved. The patterns, depth diameters, and other manufacturingprocess settings generate a designed surface topography 80 havingthree-dimensional contour, directional stability, and long-term success.The addition of general acid or abrasive media post machiningpreparation provides the benefits of refining the surface, removingsharp edges resulting from the machining, and adding a micro texture tothe implant integration surface.

Exemplary embodiments of the implant body comprise many various bodiesof various sizes and biocompatible materials that have surfaceenhancements consistent with the designed surface topography 80 ofmachined and acid etching refined surfaces. The designed surfacetopography 80 can be formed in multiple steps using very small toolingoften referred to as micro drills or milling cutters in high speed,highly precise, milling equipment. These practices are contrary tocommon efforts to remove large amounts of material as quickly aspossible. Optimization of the surface geometry and the ability to definerepeating patterns to predefined depths is beneficial to the overallproduct design can be achieved using these processes and others.

The following exemplary process steps are included to more clearlydemonstrate the overall nature of the invention. These steps areexemplary, not restrictive, of the invention. The sequential processsteps shown in FIGS. 4A, 4B, and 4C illustrate multiple layers and stepsof implant machining.

As shown in FIG. 4A, the first process step creates a first feature 82of the designed surface topography 80 on the top surface 10 of theimplant 1. The first feature 82 is typically the deepest feature of thedesigned surface topography 80 and may be, for example, 0.021 inchesdeep (or more) into the surface of the implant 1 (along the Z axis asillustrated). A wide variety of processes can be applied to create thefirst feature 82. As illustrated, the first feature is a sphericalindent which might be created, for example, by the use of a ball-shapedtool (e.g., by “peening” or drilling). In processing circumstances wheresurface material is displaced to create surface topography it will beunderstood that subsequent processing or finishing steps e.g.,polishing, may be employed to remove incidentally-created surfaceartifacts which are not part of the feature.

The designed surface topography 80 of the implant 1 is produced byoverlapping several features. In FIG. 4B, the second process stepcreates a second feature 84 of the designed surface topography 80 of theimplant 1 but up to the depth of the first feature. The second feature84 is typically the second deepest feature of the designed surfacetopography 80 and may be, for example, 0.014 inches deep into thesurface of the implant 1. A wide variety of processes can be applied tocreate the second feature 84. The depth and X-Y placement of the secondfeature 84 are selected so that the second feature 84 does not directlyoverlap and wipe out the first feature 82 (to highlight the secondfeature 84 and for purposes of clarity the first feature 82 is not shownin FIG. 4B although the first feature 82 exists in combination with thesecond feature 84). The depth variations and alignment to the expectedload direction will have the same net effect as a single feature of thesame depth, but in other lower loaded directions will minimize focusedloading and reduce stresses that the bone is subjected to when lowerloading is applied. As with the first feature 82 incidentally-createdprocess artifacts e.g., burrs, splays, may need to be removed using wellknown techniques.

As shown in FIG. 4C, the third process step creates a third feature 86of the designed surface topography 80 of the implant 1. The thirdfeature 86 is typically the shallowest feature of the designed surfacetopography 80 and may be, for example, 0.007 inches deep into thesurface of implant 1 but less than the depth of the second feature 84. Awide variety of processes can be applied to create the third feature 86.The depth and X-Y placement of the third feature 86 are selected so thatthe third feature 86 does not directly overlap and wipe out the firstfeature 82 or the second feature 84 (to highlight the third feature 86and for purposes of clarity the first feature 82 and the second feature84 are not shown in FIG. 4C although the first feature 82 and the secondfeature 84 exist in combination with the third feature 86). Note thatthe right-most column of the third feature 86 as illustrated in FIG. 4Cappears smaller than the remainder of the third feature 86 only becausethe third feature 86 extends beyond the top surface 10 and onto thelateral side 30 a short distance.

Of course, processes with more or fewer than three steps can be used tocreate any predetermined pattern for the designed surface topography 80.And each process step can create a feature that differs (in type, size,shape, location, and other characteristics) from the featuresillustrated in FIGS. 4A, 4B, and 4C. FIGS. 4A, 4B, and 4C depictexemplary process steps with different surfaces. As completed for theexample illustrated, the designed surface topography 80 following themulti-step sequential application of process steps (shown as bracket 88and indicating the completed workpiece or working surface) and finalworking surface of implant body 5 is shown in FIG. 4D. The implant 1illustrated in FIG. 4D combines machined and acid etched micro surfacesthat behave in a similar manner with regard to the bone tissues, but adddirectional stability by having an organized pattern that resistsloading and potential movement of the implant 1.

The designed surface topography 80 of the implant 1 is produced byoverlapping several features. This results in a large surface area ofdefined geometric shapes and patterns. Preferably, the process stepsinclude repeating shapes between the machining steps to produce a largesurface area having a defined pattern. The designed surface topography80 may also be refined using mechanical, focused energy or chemicalprocesses to improve the implant surface.

Thus, the designed surface topography 80 may be obtained through avariety of techniques including, without limitation, chemical or acidetching, shot peening, plasma etching, laser etching, or abrasiveblasting, such as sand or grit blasting. In one process step embodimentof the present invention, a roughened surface topography is obtained viathe repetitive masking and chemical or electrochemical milling processesdescribed in U.S. Pat. No. 5,258,098; No. 5,507,815; No. 5,922,029; andNo. 6,193,762, each incorporated herein by reference. By way of example,an etchant mixture of nitric acid and hydrofluoric acid (HF) may berepeatedly applied to a titanium surface to produce an average etchdepth of about 0.021 inches. Interbody spinal implants 1 may becomprised, in accordance with preferred embodiments of the presentinvention, of titanium or a titanium alloy having an average surfaceroughness of about 100 μm on the top surface 10 and on the bottomsurface 20. Surface roughness may be measured using a laser profilometeror other standard instrumentation.

The implant surface is produced using defined and adapted tooling that,when patterns of these features are overlapped in a predeterminedmanner, result in an improved surface capable of sustaining osseousin-growth under loading. Various chemicals, such as acids, may be usedto refine the contours of the implant surface. The result of suchrefinement is a relatively smooth surface free from manufacturing debrisand well adapted to biological behavior of bone tissues.

Due to their small size and limited operational access, implants 1 ofthe exemplary type are typically difficult to manipulate and preciselyplace without instruments. The body of the implant typically includes atleast three, and sometimes more than three, instrument connections (suchas the opening 90) that can be threaded, force fit, or snap fit togetherto rigidly connect the implant 1 and withstand placement in thevertebrae. The force fit of the implant 1 into the intravertebral spacecreates initial stability of the device and incorporates the bonetissues into the surface of the implant 1.

Examples Background

Titanium implants with physical-chemical modifications such as micron orsubmicron scale topographic features have been shown to increaseosteoblast differentiation and local factor production in vivo and toincrease pen-implant bone formation and decrease healing time in vivo.Polyetheretherketone (PEEK) is used as a cage or spacer in vertebralinterbody fusion to maintain spinal alignment and segmental stabilitywhile facilitating bony fusion. The aim of this analysis was toelucidate whether common intervertebral materials such as PEEK andtitanium alloy (Ti6AI4V) induce osteoblast maturation and generate anosteogenic environment.

Methods

The methods employed herein are shown below.

Human osteoblast-like MG63 cells were cultured on tissue culturepolystyrene (TCPS), PEEK, or smooth [sTi6AI4V, Sa>90 nm] and rough[rTi6AI4V, Sa=1.81 μm] Ti6AI4V surfaces as shown in FIG. 9. Geneexpression was measured by qPCR. Osteoblast maturation was assessed byanalysis of cell number, alkaline phosphatase activity (ALP), andsecreted osteocalcin, osteoprotegerin, TGF-B1, BMP2, BMP4, and BMP7.Data are mean±SEM (n=6/condition), analyzed by ANOVA with Bonferroni'smodification of Student's t-test.

Results

FIGS. 5A, 5B, and 5C. Confocal laser microscopy images andaverage-roughness (S_(a)) values of PEEK (A), sTiAIV (B), and rTiAIV (C)surfaces of 644×644 μm² field.

FIGS. 6A, 6B, 6C, 6D, 6E, and 6F. SEM images of PEEK (A, B), sTiAIV (C,D), and rTiAIV (E, F) surfaces at low and high magnifications.

Human MG63 osteoblast-like cells were harvested 24 hours afterconfluence on TCPS.

Cell number, alkaline phosphatase specific activity in cell lysates andlevels of osteocalcin, osteoprotegerin, active TGF-β1, latent TGF-β1,BMP2 and BMP4 in the conditioned media were measured. *p<0.05, v. TCPS;#p<0.05, v. PEEK; $p<0.05, v. sTiAIV. The values obtained are shown inFIGS. 10A-D and FIGS. 11-A-D.

Human MG63 osteoblast-like cells were harvested 12 hours afterconfluence on TCPS. Levels of mRNA for integrins alpha 1 (ITGA1), alpha2 (ITGA2), alpha v (ITGAV), and beta 1 (ITGB1), BMP2 (A) and BMP4, andBMP inhibitors noggin (NOG) and gremlin 1 (GREM1) were measured byreal-time qPCR and normalized to GAPDH. *p<0.05, v. TCPS; #p<0.05, v.PEEK; $p<0.05, v. sTiAIV. Results are shown in FIGS. 12A-H.

Discussion

The results indicate that osteoblasts on Ti6AI4V surfaces present a moremature phenotype than osteoblasts grown on PEEK. Cells on Ti6AI4V, butnot PEEK, produce an osteogenic environment. Osteoblasts cultured onTi6AI4V produce and regulate BMP pathway molecules, increasing BMP2,BMP4, BMP7, and physiologic BMP inhibitors. One reason for thedifferential response of osteoblasts to PEEK and TiALV may result fromdifferences in integrin expression downstream signaling by thesereceptors. Taken together, surface properties, including the compositionof the bulk material, are important in directing cell response toimplant materials, ultimately affecting implant success. The resultsdemonstrate that Ti6AI4V surfaces positively modulate osteoblastmaturation and regulate BMP signaling.

The instrumentation and installation practices of this invention areused in not only spinal surgery, but also in common orthopedic treatmentof many of the bones and joints in the body. Common hip and kneeimplants often use a force fit or interference fit to initiallystabilize the implants and promote long-term success. These instrumentsand the connection to the implants are correspondingly durable androbust enough to withstand loading, impacts, and forces resulting fromthe procedures.

Although illustrated and described above with reference to certainspecific embodiments and examples, the present invention is neverthelessnot intended to be limited to the details shown. Rather, variousmodifications may be made in the details within the scope and range ofequivalents of the claims and without departing from the spirit of theinvention. It is expressly intended, for example, that all rangesbroadly recited in this document include within their scope all narrowerranges which fall within the broader ranges.

1. An implantable device, comprising a body having a top surface and abottom surface, the top surface, the bottom surface, or both the top andbottom surfaces having a surface topography comprising first, second,and third surface patterns without sharp protrusions; the first surfacepattern including a plurality of dimples having a first depth dimension,the second surface pattern including a plurality of dimples having asecond depth dimension, and the third surface pattern including aplurality of dimples having a third depth dimension, the first depthdimension being greater than the second depth dimension, and the seconddepth dimension being greater than the third depth dimension, wherein aportion of the second surface pattern overlaps the first surface patternand a portion of the second surface pattern does not overlap the firstsurface pattern, and a portion of the third surface pattern overlaps thesecond surface pattern and a portion of the third surface pattern doesnot overlap the second surface pattern, and wherein the third surfacepattern supports in-growth of bone into the body.
 2. The implantabledevice of claim 1, wherein the surface topography is oriented to havehigher load resistance to a specific load direction.
 3. The implantabledevice of claim 1, wherein the plurality of dimples of the first surfacepattern and of the second surface pattern comprises semi-spheres.
 4. Theimplantable device of claim 1, wherein the first surface patterncomprises macro sized features and the second surface pattern comprisesmicro sized features.
 5. The implantable device of claim 1, wherein thefirst surface pattern comprises macro sized features, the second surfacepattern comprises micro sized features, and the third surface patterncomprises nano sized features.
 6. The implantable device of claim 5,wherein the macro sized features have a macro size Rz of 50 μm to 200 μmand a roughness Ra of 10 μm to 30 μm, the micro sized features have amicro size Rz of 500 nm to 20 μm and a roughness Ra of 5 μm to 10 μm,and the nano sized features have a nano size Rz of 200 nm to 500 nm anda roughness Ra of 0.5 μm to 5 μm.
 7. The implantable device of claim 1,wherein the body comprises titanium or an alloy thereof.
 8. Theimplantable device of claim 1, wherein the surface topography issubstantially uniform across the top surface, the bottom surface, orboth the top and bottom surfaces.
 9. The implantable device of claim 1,wherein the third surface pattern positively modulates osteoblastmaturation and regulates bone morphogenic protein signaling.
 10. Theimplantable device of claim 1, wherein the first and second surfacepatterns stabilize the body when the top surface, bottom surface, orboth the top and bottom surfaces contact bone.
 11. An implantabledevice, comprising a body having a top surface and a bottom surface, thetop surface, the bottom surface, or both the top and bottom surfaceshaving a surface topography comprising first, second, and third surfacepatterns without sharp protrusions; the first surface pattern includinga plurality of dimples having a first depth dimension, the secondsurface pattern including a plurality of dimples having a second depthdimension, and the third surface pattern including a plurality ofdimples having a third depth dimension, the first depth dimension beinggreater than the second depth dimension, and the second depth dimensionbeing greater than the third depth dimension, wherein a portion of thefirst surface pattern partially overlaps the second surface pattern anda portion of the third surface pattern partially overlaps the secondsurface pattern, and wherein the third surface pattern supportsin-growth of bone into the body.
 12. The implantable device of claim 11,wherein the surface topography is oriented to have higher loadresistance to a specific load direction.
 13. The implantable device ofclaim 11, wherein the plurality of dimples of the first surface patternand of the second surface pattern comprises semi-spheres.
 14. Theimplantable device of claim 11, wherein the first surface patterncomprises macro sized features and the second surface pattern comprisesmicro sized features.
 15. The implantable device of claim 11, whereinthe first surface pattern comprises macro sized features, the secondsurface pattern comprises micro sized features, and the third surfacepattern comprises nano sized features.
 16. The implantable device ofclaim 15, wherein the macro sized features have a macro size Rz of 50 μmto 200 μm and a roughness Ra of 10 μm to 30 μm, the micro sized featureshave a micro size Rz of 500 nm to 20 μm and a roughness Ra of 5 μm to 10μm, and the nano sized features have a nano size Rz of 200 nm to 500 nmand a roughness Ra of 0.5 μm to 5 μm.
 17. The implantable device ofclaim 11, wherein the body comprises titanium or an alloy thereof. 18.The implantable device of claim 11, wherein the surface topography issubstantially uniform across the top surface, the bottom surface, orboth the top and bottom surfaces.
 19. The implantable device of claim11, wherein the third surface pattern positively modulates osteoblastmaturation and regulates bone morphogenic protein signaling.
 20. Theimplantable device of claim 11, wherein the first and second surfacepatterns stabilize the body when the top surface, bottom surface, orboth the top and bottom surfaces contact bone.